US20130043170A1 - Microfluidic ultrasonic particle separators with engineered node locations and geometries - Google Patents
Microfluidic ultrasonic particle separators with engineered node locations and geometries Download PDFInfo
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- US20130043170A1 US20130043170A1 US13/571,640 US201213571640A US2013043170A1 US 20130043170 A1 US20130043170 A1 US 20130043170A1 US 201213571640 A US201213571640 A US 201213571640A US 2013043170 A1 US2013043170 A1 US 2013043170A1
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- B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
- B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
- B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
- B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
- B01L3/50273—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by the means or forces applied to move the fluids
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D21/00—Separation of suspended solid particles from liquids by sedimentation
- B01D21/28—Mechanical auxiliary equipment for acceleration of sedimentation, e.g. by vibrators or the like
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D21/00—Separation of suspended solid particles from liquids by sedimentation
- B01D21/28—Mechanical auxiliary equipment for acceleration of sedimentation, e.g. by vibrators or the like
- B01D21/283—Settling tanks provided with vibrators
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
- B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
- B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
- B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
- B01L3/502761—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip specially adapted for handling suspended solids or molecules independently from the bulk fluid flow, e.g. for trapping or sorting beads, for physically stretching molecules
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N1/00—Sampling; Preparing specimens for investigation
- G01N1/28—Preparing specimens for investigation including physical details of (bio-)chemical methods covered elsewhere, e.g. G01N33/50, C12Q
- G01N1/40—Concentrating samples
- G01N1/4077—Concentrating samples by other techniques involving separation of suspended solids
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/48707—Physical analysis of biological material of liquid biological material by electrical means
- G01N33/48728—Investigating individual cells, e.g. by patch clamp, voltage clamp
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/49—Blood
- G01N33/491—Blood by separating the blood components
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D2221/00—Applications of separation devices
- B01D2221/10—Separation devices for use in medical, pharmaceutical or laboratory applications, e.g. separating amalgam from dental treatment residues
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
- B01L2200/06—Fluid handling related problems
- B01L2200/0631—Purification arrangements, e.g. solid phase extraction [SPE]
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
- B01L2200/06—Fluid handling related problems
- B01L2200/0636—Focussing flows, e.g. to laminate flows
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
- B01L2200/06—Fluid handling related problems
- B01L2200/0647—Handling flowable solids, e.g. microscopic beads, cells, particles
- B01L2200/0652—Sorting or classification of particles or molecules
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2300/00—Additional constructional details
- B01L2300/08—Geometry, shape and general structure
- B01L2300/0809—Geometry, shape and general structure rectangular shaped
- B01L2300/0816—Cards, e.g. flat sample carriers usually with flow in two horizontal directions
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2300/00—Additional constructional details
- B01L2300/08—Geometry, shape and general structure
- B01L2300/0861—Configuration of multiple channels and/or chambers in a single devices
- B01L2300/0864—Configuration of multiple channels and/or chambers in a single devices comprising only one inlet and multiple receiving wells, e.g. for separation, splitting
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/04—Moving fluids with specific forces or mechanical means
- B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
- B01L2400/0433—Moving fluids with specific forces or mechanical means specific forces vibrational forces
- B01L2400/0439—Moving fluids with specific forces or mechanical means specific forces vibrational forces ultrasonic vibrations, vibrating piezo elements
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/04—Moving fluids with specific forces or mechanical means
- B01L2400/0475—Moving fluids with specific forces or mechanical means specific mechanical means and fluid pressure
- B01L2400/0487—Moving fluids with specific forces or mechanical means specific mechanical means and fluid pressure fluid pressure, pneumatics
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N1/00—Sampling; Preparing specimens for investigation
- G01N1/28—Preparing specimens for investigation including physical details of (bio-)chemical methods covered elsewhere, e.g. G01N33/50, C12Q
- G01N1/40—Concentrating samples
- G01N1/4077—Concentrating samples by other techniques involving separation of suspended solids
- G01N2001/4094—Concentrating samples by other techniques involving separation of suspended solids using ultrasound
Definitions
- the present invention relates to microfluidic particle separators and more particularly to microfluidic ultrasonic particle separators with engineered node locations and geometries.
- the article includes the state of technology information quoted below and drawing FIGS. 1A , 1 B, and 1 C are copies of FIGS. 5 , 6 and 7 from the article.
- the article, “Chip integrated strategies for acoustic separation and manipulation of cells and particles,” by Thomas Laurell, Filip Petersson and Andreas Nilsson in Chem. Soc. Rev., 2007, 36, 492-506, is incorporated herein in its entirety for all purposes.
- FIG. 5 Schematic cross-section of separation chip utilizing the Lund method.
- the silicon separation channel is sealed by a boron silica glass lid and is actuated from below using a piezoelectric ceramic.
- FIG. 6 Illustrated cross-section (along the dashed line in FIG. 7 ) of a separation channel showing negative w-factor particles (e.g. lipid particles) collected in the pressure antinodes by the side walls and positive w-factor particles (i.e. red blood cells) in the pressure node.”
- negative w-factor particles e.g. lipid particles
- positive w-factor particles i.e. red blood cells
- FIG. 7 Illustration of separation of negative w-factor particles (black—centre outlet) and positive w-factor particles (grey—side outlets) in 45 u design chip. [ FIG. 1C ]
- the Lund-method for acoustic separation of suspended particles from their medium is based on a laminar flow microchannel that is ultrasonically actuated from below, using a piezoelectric ceramic ( FIG. 5 ).
- the width of the channel is chosen to correspond to half the ultrasonic wavelength, thereby creating a resonator between the side walls of the flow channel in which a standing wave can be formed.
- the induced standing wave is thus generated orthogonal to the incident ultrasonic wave front.
- suspended particles with a positive w-factor perfuse the channel they are moved, by means of the axial PRF, towards the pressure nodal plane along the channel centre, while those with a negative w-factor are moved towards the anti-nodal planes close to the side walls (FIG. 6 ).
- the end of the separation channel is split into three outlet channels, thus allowing the positive w-factor particles to exit through the centre outlet and the negative w-factor particles to exit through the side outlets, provided that all outlet flow rates are alike ( FIG. 7 ).
- the separation efficiency of positive and negative w-factor particles is defined as the fraction of particles exiting through the centre and side outlets respectively.”
- the present invention provides high-throughput sample processing of biological material.
- the system of the present invention separates out cell-sized particles from a background solution containing other biological materials (viruses, proteins, nucleic acids, etc.) in order to allow uncontaminated analysis of either the background sample or the separated cells.
- the present invention uses the vibrations of a piezoelectric transducer to produce acoustic radiation forces within microfluidic channels.
- the system of the present invention positions a single stream of concentrated particles off-center in the fluid channel. This is highly advantageous for achieving improved separation between the two sample fractions, and greater purity within each fraction.
- the stream of concentrated particles is positioned off-center in the separation channel by Means of subdividing the channel with one or more thin acoustically transparent walls. In another embodiment the stream of concentrated particles is positioned off-center in the fluid flow with the aid of a polymer gel structure positioned adjacent to the fluid channel.
- the pressure field resulting from the acoustic waves can be optimized by driving the piezoelectric transducer at multiple frequencies on a single device. Additionally, in these embodiments, or in any other, the separation channel can be routed in a serpentine fashion to pass multiple times (3, 5, etc.) through the ultrasound region, thereby providing a longer residence time for the sample in the acoustic field, increasing separation efficiency.
- the present invention provides an ultrasonic microfluidic system for separating smaller particles from larger particles suspended in a sample fluid.
- This sample fluid flows down a separation channel, side-by-side with a “recovery buffer,” which is typically a fluid into which the larger particles of interest are to be transferred.
- the two fluid streams are in contact with each other, but mixing is limited only to diffusion due to the low Reynolds number of microfluidic flows.
- An acoustic transducer in contact with the microfluidic chip produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, the acoustic transducer generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven.
- a second fluid channel (“bypass channel”) is located substantially parallel to the separation channel.
- a wall that is thin enough to negligibly effect the transmission of ultrasound between the bypass and separation channel (“acoustically transparent wall”) is located between the two channels.
- the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel.
- the present invention enables improved operation of the acoustic separation module within the context of a Microfluidic Sample Preparation Platform that aims to purify, separate, and fractionate different classes of particles (mammalian and bacterial cells, nucleic acids, viruses, etc.) from complex biological samples for both clinical (blood, urine, saliva, etc.) and environmental analysis (food, water, aerosol, etc.). These analyses have obvious applications in areas such as biothreat detection, pathogen identification, epidemic monitoring, virology, and vaccine production, among others.
- the present invention can be used on its own or in conjunction with other sample processing steps to prepare biological samples before they are introduced into a great variety of commercial instruments for manipulating or analyzing biological samples, such as DNA sequencing, PCR, flow cytometry, microorganism detection, etc.
- FIGS. 1A , 1 B, and 1 C are copies of FIGS. 5 , 6 and 7 from the article, “Chip integrated strategies for acoustic separation and manipulation of cells and particles,” by Thomas Laurell, Filip Petersson, and Andreas Nilsson in Chem. Soc. Rev., 2007, 36, 492-506.
- FIGS. 2A and 2B illustrate an embodiment of the invention wherein a transducer produces a single node.
- FIGS. 3A and 3B illustrate another embodiment of the invention wherein a transducer produces two nodes.
- FIGS. 4A and 4B illustrate another embodiment of the invention wherein a transducer produces two nodes, while the separation channel is designed to be narrower than the bypass channel.
- FIGS. 5A and 5B illustrate another embodiment of the invention wherein the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel.
- the present invention concerns the use of ultrasound to manipulate particles for the purposes of separating, preparing and analyzing clinical or environmental samples containing mixtures of biological particles (spores, cells, bacteria, viruses, molecules, etc.).
- biological particles spores, cells, bacteria, viruses, molecules, etc.
- the acoustical device when implemented within a fieldable, automated, continuous-flow system, the acoustical device is used to concentrate and filter out the largest particles.
- the device is highly robust and minimally sensitive to parameter variation to interface with downstream assays or other separation elements.
- the present invention can be used on its own or in conjunction with other sample processing steps to prepare biological samples before they are introduced into a great variety of commercial instruments for manipulating or analyzing biological samples, such as DNA sequencing, PCR, flow cytometry, microorganism detection, etc.
- An ultrasonic particle manipulation in microfluidic device is realized using a piezoelectric transducer to generate acoustic standing waves within a microchannel.
- the primary acoustic radiation forces induced by the sound waves direct particles toward the pressure-field minima (nodes) or maxima (antinodes), depending on the relative compressibility and density between the particle and the suspending liquid.
- the radiation forces which scale with particle volume
- the induced motions are sufficient to achieve continuous, high-throughput separation for particles of diameter greater than about 2 micrometers.
- FIG. 2A one embodiment of the present invention is illustrated.
- the device uses multiple microfluidic channels running in parallel along the length of a microfluidic chip, separated by specifically-designed distances (the “wall thickness”).
- One of these multiple channels serves as the separation channel and has two inlets and two outlets.
- the ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the recovery fluid within the recovery fluid channel.
- the piezoelectric transducer may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry.
- multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip.
- the present invention provides an ultrasonic microfluidic system for separating smaller particles from larger particles suspended in a sample fluid.
- This sample fluid flows down a separation channel, side-by-side with a “recovery buffer,” which is typically a fluid into which the larger particles of interest are to be transferred.
- the two fluid streams are in contact with each other, but mixing is limited only to diffusion due to the low Reynolds number of microfluidic flows.
- An acoustic transducer in contact with the microfluidic chip produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, the acoustic transducer generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven.
- a second fluid channel (“bypass channel”) is located substantially parallel to the separation channel.
- a wall that is thin enough to negligibly effect the transmission of ultrasound between the bypass and separation channel (“acoustically transparent wall”) is located between the two channels.
- the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel.
- the embodiment illustrated in FIG. 2A is designated generally by the reference numeral 200 .
- the device 200 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets.
- One of the two fluids contains the sample 212
- the other fluid is a “recovery” buffer 208 , which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system.
- Channel depth typically 100-300 micrometers
- width typ. 300-1000 micrometers
- wall thickness typ.
- the present invention provides an ultrasonic microfluidic apparatus for separating small particles 218 from large particles 220 contained in the sample fluid 212 .
- a sample input channel 214 is provided for conveying the sample fluid 212 containing small particles 218 and large particles 220 toward the separation area.
- a recovery fluid input channel 206 containing recovery fluid 208 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, the recovery fluid contacts the sample fluid 212 .
- a bypass fluid channel 204 containing bypass fluid 202 is located substantially parallel and adjacent the separation channel 206 .
- An acoustically transparent wall 222 is located between the bypass channel 204 and the separation channel 206 .
- the bypass channel 204 together with the wall 222 comprise an acoustic extension structure.
- An acoustic transducer 228 in contact with the microfluidic chip 216 produces an ultrasound pressure field throughout the fluids 202 , 208 , and 212 .
- the acoustic transducer 228 Properly tuned to match the geometric parameters of the channel, the acoustic transducer 228 generates a resonant standing wave within the fluids 202 , 208 , and 212 ; creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven.
- the forces that particles experience are dependent on particle size; therefore, the largest particles 220 move toward the node 224 fastest.
- Positioning the node 224 within the recovery fluid 208 stream allows the largest particles 220 to be carried out of the chip 216 with the recovery fluid 208 , separating them from other sample components that remain in the sample 212 stream.
- the body of the chip 216 includes a glass cover plate 226 .
- the body of the chip 216 and the glass cover plate 226 enclose the bypass fluid channel 204 , the bypass fluid 202 , the recovery fluid 208 , and the sample fluid 212 .
- the acoustically transparent wall 222 maintains the bypass fluid 208 separate from the sample 212 and recovery fluid 208 in the separation channel.
- the acoustic transducer 228 produces the single acoustic node 224 , designed to lie within the recovery fluid 208 stream so that the recovery fluid 208 receives the large particles 220 that are concentrated at the acoustic node 224 causing them to be carried by the recovery fluid 208 out of the “large particle” outlet (LPO) 230 .
- LPO large particle outlet
- the device uses multiple microfluidic channels running in parallel along the length of a microfluidic chip 316 , separated by specifically-designed distances (the “wall thickness”).
- One of these multiple channels serves as the separation channel and has two inlets and two outlets.
- the ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the adjacent recovery fluid stream, which flow together down the separation channel.
- the piezoelectric transducer 314 may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry.
- multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip.
- the present invention provides an ultrasonic microfluidic system for separating smaller particles 318 from larger particles 326 suspended in a sample fluid 312 .
- This sample fluid 312 flows down a separation channel 310 , side-by-side with a “recovery buffer 308 ,” which is typically a fluid into which the larger particles 326 of interest are to be transferred.
- the two fluid streams, 312 and 308 are in contact with each other, but mixing is limited only to diffusion due to the low Reynolds number of microfluidic flows.
- An acoustic transducer 314 in contact with the microfluidic chip 316 produces an ultrasound pressure field throughout these fluids.
- the acoustic transducer 314 Properly tuned to match the geometric parameters of the channel, the acoustic transducer 314 generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven.
- the forces that particles experience are dependent on particle size; therefore, the largest particles 316 move toward the nodes 324 b and 324 a fastest.
- Positioning the node 324 b within the recovery fluid 308 stream allows the largest particles 326 to be carried out of the chip 316 with the recovery fluid 308 , separating them from other sample components that remain in the sample 212 stream.
- a second fluid channel (“bypass channel 304 ”) is located substantially parallel to the separation channel.
- a wall 322 that is thin enough to negligibly effect the transmission of ultrasound between the bypass and separation channel (“acoustically transparent wall 322 ”) is located between the two channels.
- the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel.
- the present invention enables improved operation of the acoustic separation module within the context of a Microfluidic Sample Preparation Platform that aims to purify, separate, and fractionate different classes of particles (mammalian and bacterial cells, nucleic acids, viruses, etc.) from complex biological samples for both clinical (blood, urine, saliva, etc.) and environmental analysis (food, water, aerosol, etc.). These analyses have obvious applications in areas such as biothreat detection, pathogen identification, epidemic monitoring, virology, and vaccine production, among others.
- the present invention can be used on its own or in conjunction with other sample processing steps to prepare biological samples before they are introduced into a great variety of commercial instruments for manipulating or analyzing biological samples, such as DNA sequencing, PCR, flow cytometry, microorganism detection, etc.
- the embodiment illustrated in FIG. 3A is designated generally by the reference numeral 300 .
- the device 300 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets.
- One of the two fluids is the sample 312
- the other fluid is a “recovery” buffer 308 , which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system.
- Channel depth typically 100-300 micrometers
- width typ. 300-1000 micrometers
- wall thickness typ.
- the present invention provides an ultrasonic microfluidic apparatus for separating small particles 318 from large particles 326 contained in the sample fluid 312 .
- a sample input channel 310 is provided for conveying the sample fluid 312 containing small particles 318 and large particles 326 toward the separation area.
- a recovery fluid input channel 306 containing recovery fluid 308 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, the recovery fluid 308 contacts the sample fluid 312 .
- a bypass fluid channel 302 containing bypass fluid 304 is located substantially parallel and adjacent the separation channel.
- An acoustically transparent wall 322 is located between the bypass channel 302 and the separation channel. The bypass channel 302 together with the wall 322 comprise an acoustic extension structure.
- An acoustic transducer 314 in contact with the microfluidic chip 316 produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, the acoustic transducer 314 generates a resonant standing wave within the fluids, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, the largest particles 326 move toward the node fastest. Positioning the node 324 b within the recovery fluid 312 stream allows the largest particles 326 to be carried out of the chip 316 with the recovery fluid 308 , separating them from other sample components that remain in the sample 312 stream.
- the body of the chip 316 includes a glass cover plate 126 .
- the body of the chip 316 and the glass cover plate 126 enclose the bypass fluid channel 304 , the bypass fluid 302 , the recovery fluid 308 , and the sample fluid 312 .
- the acoustically transparent wall 322 maintains the bypass fluid 302 separate from the sample fluid 308 .
- the acoustic transducer 314 produces the two acoustic nodes 324 a and 324 b such that the first node 32 b is located in the recovery fluid 308 stream so that the recovery fluid 308 receives the large particles 326 that are concentrated at the first node 324 b causing them to be carried by the recovery fluid 308 out of the “large particle” outlet (LPO) 330 .
- the second node 324 a is located in the bypass channel 304 , and does not participate in the separation.
- the device uses multiple microfluidic channels running in parallel along the length of a microfluidic chip, separated by specifically-designed distances (the “wall thickness”).
- One of these multiple channels serves as the separation channel and has two inlets and two outlets.
- the ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the recovery fluid within the recovery fluid channel.
- the piezoelectric transducer may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry.
- multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip.
- the embodiment illustrated in FIG. 4A is designated generally by the reference numeral 400 .
- the device 400 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets.
- One of the two fluids is the sample fluid 412
- the other fluid is a “recovery” buffer 408 , which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system.
- Channel depth typically 100-300 ⁇ m
- width typ. 300-1000 ⁇ m
- wall thickness typ.
- the present invention provides an ultrasonic microfluidic apparatus for separating small particles 418 from large particles 420 contained in the sample fluid 412 .
- a sample input channel 410 is provided for conveying the sample fluid 412 containing small particles 418 and large particles 420 toward the separation area.
- a recovery fluid input channel 406 containing recovery fluid 408 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, the recovery fluid 408 contacts the sample fluid 412 .
- a bypass fluid channel 204 containing bypass fluid 204 is located substantially parallel and adjacent the separation channel. Note that the bypass fluid channel is a wide channel compared to the bypass channel shown in the previously described embodiments.
- An acoustically transparent wall 422 is located between the bypass channel 204 and the separation channel 406 .
- the bypass channel 404 together with the wall 422 comprise an acoustic extension structure.
- An acoustic transducer 414 in contact with the microfluidic chip 416 produces an ultrasound pressure field throughout these fluids.
- the acoustic transducer 414 Properly tuned to match the geometric parameters of the channel, the acoustic transducer 414 generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven.
- the forces that particles experience are dependent on particle size; therefore, the largest particles 420 move toward the node 424 b fastest.
- Positioning the node 424 b within the recovery fluid 408 stream allows the largest particles 420 to be carried out of the chip 416 with the recovery fluid 408 , separating them from other sample components that remain in the sample 412 stream.
- the body of the chip 416 includes a glass cover plate 426 .
- the body of the chip 416 and the glass cover plate 126 enclose the bypass fluid channel 404 , the bypass fluid 402 , the recovery fluid 408 , and the sample fluid 412 .
- the acoustically transparent wall 422 maintains the bypass fluid 402 separate from the recovery fluid 408 .
- the acoustic transducer 414 produces the acoustic nodes 424 a and 424 b .
- the first node 424 a is located in the recovery fluid 408 stream so that the recovery fluid 408 receives the large particles 420 that are concentrated at the first acoustic node 424 a causing them to be carried by the recovery fluid 408 out of the “large particle” outlet (LPO) 430 .
- the second node 424 b is located in the bypass channel and does not participate in the separation.
- FIG. 5A another embodiment of the invention is illustrated wherein the stream of concentrated particles is positioned off-center in the fluid channel by means of a region of hydrogel adjacent the fluid channel.
- a hydrogel is immobilized (by photopolymerization or by other means) within the searation channel.
- the ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the recovery fluid within the recovery fluid channel.
- the piezoelectric transducer may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry.
- multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip.
- the embodiment illustrated in FIG. 5A is designated generally by the reference numeral 500 .
- the device 500 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets.
- One of the two fluids, the sample fluid 512 contains the sample and the other fluid is a “recovery” buffer 508 , which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system.
- Channel depth typically 100-300 micrometers
- width typ. 300-1000 micrometers
- wall thickness typ.
- the present invention provides an ultrasonic microfluidic apparatus for separating small particles 518 from large particles 520 contained in the sample fluid 512 .
- a sample input channel 510 is provided for conveying the sample fluid 512 containing small particles 518 and large particles 520 toward the separation area.
- a recovery fluid input channel 506 containing recovery fluid 508 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, the recovery fluid contacts the sample fluid 512 .
- a gel 502 is located substantially parallel and adjacent the separation channel 506 .
- the gel 502 comprises an acoustic extension structure.
- An acoustic transducer 514 in contact with the microfluidic chip 516 produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, the acoustic transducer 514 generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, the largest particles 420 move toward the node 424 fastest. Positioning the node 524 within the recovery fluid 508 stream allows the largest particles 520 to be carried out of the chip 516 with the recovery fluid 508 , separating them from other sample components that remain in the sample stream.
- the body of the chip 516 includes a glass cover plate 126 .
- the body of the chip 516 and the glass cover plate 126 enclose the gel 528 , the recovery fluid 508 , and the sample fluid 512 .
- the acoustic transducer 514 produces the acoustic node 524 in the recovery fluid stream 506 so that the recovery fluid 508 receives the large particles 520 that are concentrated at the acoustic node 524 causing them to be carried by the recovery fluid 508 out of the “large particle” outlet (LPO) 530 .
- LPO large particle” outlet
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Abstract
Description
- This application claims benefit under 35 U.S.C. §119(e) of U.S. Provisional Patent Application No. 61/524,020 filed Aug. 16, 2011 entitled “microfluidic ultrasonic particle separators with engineered node locations and geometries,” the disclosure of which is hereby incorporated by reference in its entirety for all purposes.
- The United States Government has rights in this invention pursuant to Contract No. DE-AC52-07NA27344 between the United States Department of Energy and Lawrence Livermore National Security, LLC for the operation of Lawrence Livermore National Laboratory.
- 1. Field of Endeavor
- The present invention relates to microfluidic particle separators and more particularly to microfluidic ultrasonic particle separators with engineered node locations and geometries.
- 2. State of Technology
- The article, “Chip integrated strategies for acoustic separation and manipulation of cells and particles,” by Thomas Laurell, Filip Petersson, and Andreas Nilsson in Chem. Soc. Rev., 2007, 36, 492-506, states: “Chip integrated strategies for acoustic separation and manipulation of cells and particles,” by Thomas Laurell.” The article includes the state of technology information quoted below and drawing
FIGS. 1A , 1B, and 1C are copies ofFIGS. 5 , 6 and 7 from the article. The article, “Chip integrated strategies for acoustic separation and manipulation of cells and particles,” by Thomas Laurell, Filip Petersson and Andreas Nilsson in Chem. Soc. Rev., 2007, 36, 492-506, is incorporated herein in its entirety for all purposes. - “
FIG. 5 Schematic cross-section of separation chip utilizing the Lund method. The silicon separation channel is sealed by a boron silica glass lid and is actuated from below using a piezoelectric ceramic.” [FIG. 1A ] - “
FIG. 6 Illustrated cross-section (along the dashed line inFIG. 7 ) of a separation channel showing negative w-factor particles (e.g. lipid particles) collected in the pressure antinodes by the side walls and positive w-factor particles (i.e. red blood cells) in the pressure node.” [FIG. 1B ] - “
FIG. 7 Illustration of separation of negative w-factor particles (black—centre outlet) and positive w-factor particles (grey—side outlets) in 45 u design chip. [FIG. 1C ] - “The Lund-method for acoustic separation of suspended particles from their medium is based on a laminar flow microchannel that is ultrasonically actuated from below, using a piezoelectric ceramic (
FIG. 5 ). The width of the channel is chosen to correspond to half the ultrasonic wavelength, thereby creating a resonator between the side walls of the flow channel in which a standing wave can be formed. The induced standing wave is thus generated orthogonal to the incident ultrasonic wave front. As suspended particles with a positive w-factor perfuse the channel they are moved, by means of the axial PRF, towards the pressure nodal plane along the channel centre, while those with a negative w-factor are moved towards the anti-nodal planes close to the side walls (FIG. 6).” - “The end of the separation channel is split into three outlet channels, thus allowing the positive w-factor particles to exit through the centre outlet and the negative w-factor particles to exit through the side outlets, provided that all outlet flow rates are alike (
FIG. 7 ). The separation efficiency of positive and negative w-factor particles is defined as the fraction of particles exiting through the centre and side outlets respectively.” - Features and advantages of the present invention will become apparent from the following description. Applicants are providing this description, which includes drawings and examples of specific embodiments, to give a broad representation of the invention. Various changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from this description and by practice of the invention. The scope of the invention is not intended to be limited to the particular forms disclosed and the invention covers all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the claims.
- The present invention provides high-throughput sample processing of biological material. The system of the present invention separates out cell-sized particles from a background solution containing other biological materials (viruses, proteins, nucleic acids, etc.) in order to allow uncontaminated analysis of either the background sample or the separated cells. The present invention uses the vibrations of a piezoelectric transducer to produce acoustic radiation forces within microfluidic channels. Whereas other investigators have demonstrated technologies that position a single stream of concentrated particles on the center-line of a fluid channel, or multiple streams of particles, such that some of them are off-center, the system of the present invention positions a single stream of concentrated particles off-center in the fluid channel. This is highly advantageous for achieving improved separation between the two sample fractions, and greater purity within each fraction. In one embodiment, the stream of concentrated particles is positioned off-center in the separation channel by Means of subdividing the channel with one or more thin acoustically transparent walls. In another embodiment the stream of concentrated particles is positioned off-center in the fluid flow with the aid of a polymer gel structure positioned adjacent to the fluid channel. In these embodiments, or in any other, the pressure field resulting from the acoustic waves can be optimized by driving the piezoelectric transducer at multiple frequencies on a single device. Additionally, in these embodiments, or in any other, the separation channel can be routed in a serpentine fashion to pass multiple times (3, 5, etc.) through the ultrasound region, thereby providing a longer residence time for the sample in the acoustic field, increasing separation efficiency.
- The present invention provides an ultrasonic microfluidic system for separating smaller particles from larger particles suspended in a sample fluid. This sample fluid flows down a separation channel, side-by-side with a “recovery buffer,” which is typically a fluid into which the larger particles of interest are to be transferred. The two fluid streams are in contact with each other, but mixing is limited only to diffusion due to the low Reynolds number of microfluidic flows. An acoustic transducer in contact with the microfluidic chip produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, the acoustic transducer generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, the largest particles move toward the node fastest. Positioning the node within the recovery fluid stream allows the largest particles to be carried out of the chip with the recovery fluid, separating them from other sample components that remain in the sample stream. In one embodiment a second fluid channel (“bypass channel”) is located substantially parallel to the separation channel. A wall that is thin enough to negligibly effect the transmission of ultrasound between the bypass and separation channel (“acoustically transparent wall”) is located between the two channels. In another embodiment the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel.
- The present invention enables improved operation of the acoustic separation module within the context of a Microfluidic Sample Preparation Platform that aims to purify, separate, and fractionate different classes of particles (mammalian and bacterial cells, nucleic acids, viruses, etc.) from complex biological samples for both clinical (blood, urine, saliva, etc.) and environmental analysis (food, water, aerosol, etc.). These analyses have obvious applications in areas such as biothreat detection, pathogen identification, epidemic monitoring, virology, and vaccine production, among others. The present invention can be used on its own or in conjunction with other sample processing steps to prepare biological samples before they are introduced into a great variety of commercial instruments for manipulating or analyzing biological samples, such as DNA sequencing, PCR, flow cytometry, microorganism detection, etc.
- The invention is susceptible to modifications and alternative forms. Specific embodiments are shown by way of example. It is to be understood that the invention is not limited to the particular forms disclosed. The invention covers all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the claims.
- The accompanying drawings, which are incorporated into and constitute a part of the specification, illustrate specific embodiments of the invention and, together with the general description of the invention given above, and the detailed description of the specific embodiments, serve to explain the principles of the invention.
-
FIGS. 1A , 1B, and 1C (PRIOR ART) are copies ofFIGS. 5 , 6 and 7 from the article, “Chip integrated strategies for acoustic separation and manipulation of cells and particles,” by Thomas Laurell, Filip Petersson, and Andreas Nilsson in Chem. Soc. Rev., 2007, 36, 492-506. -
FIGS. 2A and 2B illustrate an embodiment of the invention wherein a transducer produces a single node. -
FIGS. 3A and 3B illustrate another embodiment of the invention wherein a transducer produces two nodes. -
FIGS. 4A and 4B illustrate another embodiment of the invention wherein a transducer produces two nodes, while the separation channel is designed to be narrower than the bypass channel. -
FIGS. 5A and 5B illustrate another embodiment of the invention wherein the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel. - Referring to the drawings, to the following detailed description, and to incorporated materials, detailed information about the invention is provided including the description of specific embodiments. The detailed description serves to explain the principles of the invention. The invention is susceptible to modifications and alternative forms. The invention is not limited to the particular forms disclosed. The invention covers all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the claims.
- The present invention concerns the use of ultrasound to manipulate particles for the purposes of separating, preparing and analyzing clinical or environmental samples containing mixtures of biological particles (spores, cells, bacteria, viruses, molecules, etc.). In particular, when implemented within a fieldable, automated, continuous-flow system, the acoustical device is used to concentrate and filter out the largest particles. The device is highly robust and minimally sensitive to parameter variation to interface with downstream assays or other separation elements. The present invention can be used on its own or in conjunction with other sample processing steps to prepare biological samples before they are introduced into a great variety of commercial instruments for manipulating or analyzing biological samples, such as DNA sequencing, PCR, flow cytometry, microorganism detection, etc.
- An ultrasonic particle manipulation in microfluidic device is realized using a piezoelectric transducer to generate acoustic standing waves within a microchannel. The primary acoustic radiation forces induced by the sound waves direct particles toward the pressure-field minima (nodes) or maxima (antinodes), depending on the relative compressibility and density between the particle and the suspending liquid. In general, if the radiation forces (which scale with particle volume) are directed transversely to the fluid flow direction, the induced motions are sufficient to achieve continuous, high-throughput separation for particles of diameter greater than about 2 micrometers.
- Referring now to the drawings and in particular to
FIG. 2A , one embodiment of the present invention is illustrated. - The device uses multiple microfluidic channels running in parallel along the length of a microfluidic chip, separated by specifically-designed distances (the “wall thickness”). One of these multiple channels serves as the separation channel and has two inlets and two outlets. The ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the recovery fluid within the recovery fluid channel. The piezoelectric transducer may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry. In addition, multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip.
- The present invention provides an ultrasonic microfluidic system for separating smaller particles from larger particles suspended in a sample fluid. This sample fluid flows down a separation channel, side-by-side with a “recovery buffer,” which is typically a fluid into which the larger particles of interest are to be transferred. The two fluid streams are in contact with each other, but mixing is limited only to diffusion due to the low Reynolds number of microfluidic flows. An acoustic transducer in contact with the microfluidic chip produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, the acoustic transducer generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, the largest particles move toward the node fastest. Positioning the node within the recovery fluid stream allows the largest particles to be carried out of the chip with the recovery fluid, separating them from other sample components that remain in the sample stream. In one embodiment a second fluid channel (“bypass channel”) is located substantially parallel to the separation channel. A wall that is thin enough to negligibly effect the transmission of ultrasound between the bypass and separation channel (“acoustically transparent wall”) is located between the two channels. In another embodiment the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel.
- The embodiment illustrated in
FIG. 2A is designated generally by thereference numeral 200. Thedevice 200 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets. One of the two fluids contains thesample 212, and the other fluid is a “recovery”buffer 208, which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system. Channel depth (typically 100-300 micrometers), width (typ. 300-1000 micrometers), and wall thickness (typ. 10-40 micrometers) are determined for each chip based on the desired acoustic pressure fields, and fabricated by means of standard photolithography with anisotropic etching. The two fluids enter the separation channel through separate inlets, and the separated sample fractions are collected at the two outlets. - The present invention provides an ultrasonic microfluidic apparatus for separating
small particles 218 fromlarge particles 220 contained in thesample fluid 212. Asample input channel 214 is provided for conveying thesample fluid 212 containingsmall particles 218 andlarge particles 220 toward the separation area. A recoveryfluid input channel 206 containingrecovery fluid 208 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, the recovery fluid contacts thesample fluid 212. Abypass fluid channel 204 containingbypass fluid 202 is located substantially parallel and adjacent theseparation channel 206. An acousticallytransparent wall 222 is located between thebypass channel 204 and theseparation channel 206. Thebypass channel 204 together with thewall 222 comprise an acoustic extension structure. - An
acoustic transducer 228 in contact with themicrofluidic chip 216 produces an ultrasound pressure field throughout thefluids acoustic transducer 228 generates a resonant standing wave within thefluids largest particles 220 move toward thenode 224 fastest. Positioning thenode 224 within therecovery fluid 208 stream allows thelargest particles 220 to be carried out of thechip 216 with therecovery fluid 208, separating them from other sample components that remain in thesample 212 stream. - Referring now to
FIG. 2B , a cross section taken alonglines 2B ofFIG. 2A in the direction of the arrows is shown. The body of thechip 216 includes aglass cover plate 226. The body of thechip 216 and theglass cover plate 226 enclose thebypass fluid channel 204, thebypass fluid 202, therecovery fluid 208, and thesample fluid 212. The acousticallytransparent wall 222 maintains thebypass fluid 208 separate from thesample 212 andrecovery fluid 208 in the separation channel. - The
acoustic transducer 228 produces the singleacoustic node 224, designed to lie within therecovery fluid 208 stream so that therecovery fluid 208 receives thelarge particles 220 that are concentrated at theacoustic node 224 causing them to be carried by therecovery fluid 208 out of the “large particle” outlet (LPO) 230. - Referring now to
FIG. 3A , another embodiment of the present invention is illustrated. The device uses multiple microfluidic channels running in parallel along the length of amicrofluidic chip 316, separated by specifically-designed distances (the “wall thickness”). One of these multiple channels serves as the separation channel and has two inlets and two outlets. The ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the adjacent recovery fluid stream, which flow together down the separation channel. Thepiezoelectric transducer 314 may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry. In addition, multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip. - The present invention provides an ultrasonic microfluidic system for separating
smaller particles 318 from larger particles 326 suspended in asample fluid 312. Thissample fluid 312 flows down aseparation channel 310, side-by-side with a “recovery buffer 308,” which is typically a fluid into which the larger particles 326 of interest are to be transferred. The two fluid streams, 312 and 308, are in contact with each other, but mixing is limited only to diffusion due to the low Reynolds number of microfluidic flows. Anacoustic transducer 314 in contact with themicrofluidic chip 316 produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, theacoustic transducer 314 generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, thelargest particles 316 move toward thenodes 324 b and 324 a fastest. Positioning the node 324 b within therecovery fluid 308 stream allows the largest particles 326 to be carried out of thechip 316 with therecovery fluid 308, separating them from other sample components that remain in thesample 212 stream. In one embodiment a second fluid channel (“bypass channel 304”) is located substantially parallel to the separation channel. Awall 322 that is thin enough to negligibly effect the transmission of ultrasound between the bypass and separation channel (“acousticallytransparent wall 322”) is located between the two channels. In another embodiment the stream of concentrated particles is positioned off-center in the fluid channel by means of a gel positioned adjacent the fluid channel. - The present invention enables improved operation of the acoustic separation module within the context of a Microfluidic Sample Preparation Platform that aims to purify, separate, and fractionate different classes of particles (mammalian and bacterial cells, nucleic acids, viruses, etc.) from complex biological samples for both clinical (blood, urine, saliva, etc.) and environmental analysis (food, water, aerosol, etc.). These analyses have obvious applications in areas such as biothreat detection, pathogen identification, epidemic monitoring, virology, and vaccine production, among others. The present invention can be used on its own or in conjunction with other sample processing steps to prepare biological samples before they are introduced into a great variety of commercial instruments for manipulating or analyzing biological samples, such as DNA sequencing, PCR, flow cytometry, microorganism detection, etc.
- The embodiment illustrated in
FIG. 3A is designated generally by thereference numeral 300. Thedevice 300 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets. One of the two fluids is thesample 312, and the other fluid is a “recovery”buffer 308, which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system. Channel depth (typically 100-300 micrometers), width (typ. 300-1000 micrometers), and wall thickness (typ. 10-40 micrometers) are determined for each chip based on the desired acoustic pressure fields, and fabricated by means of standard photolithography with anisotropic etching. The two fluids enter the separation channel through separate inlets, and the separated sample fractions are collected at the two outlets. - The present invention provides an ultrasonic microfluidic apparatus for separating
small particles 318 from large particles 326 contained in thesample fluid 312. Asample input channel 310 is provided for conveying thesample fluid 312 containingsmall particles 318 and large particles 326 toward the separation area. A recovery fluid input channel 306 containingrecovery fluid 308 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, therecovery fluid 308 contacts thesample fluid 312. Abypass fluid channel 302 containingbypass fluid 304 is located substantially parallel and adjacent the separation channel. An acousticallytransparent wall 322 is located between thebypass channel 302 and the separation channel. Thebypass channel 302 together with thewall 322 comprise an acoustic extension structure. - An
acoustic transducer 314 in contact with themicrofluidic chip 316 produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, theacoustic transducer 314 generates a resonant standing wave within the fluids, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, the largest particles 326 move toward the node fastest. Positioning the node 324 b within therecovery fluid 312 stream allows the largest particles 326 to be carried out of thechip 316 with therecovery fluid 308, separating them from other sample components that remain in thesample 312 stream. - Referring now to
FIG. 3B , a cross section taken alonglines 3B ofFIG. 3A in the direction of the arrows is shown. The body of thechip 316 includes aglass cover plate 126. The body of thechip 316 and theglass cover plate 126 enclose thebypass fluid channel 304, thebypass fluid 302, therecovery fluid 308, and thesample fluid 312. The acousticallytransparent wall 322 maintains thebypass fluid 302 separate from thesample fluid 308. - The
acoustic transducer 314 produces the twoacoustic nodes 324 a and 324 b such that the first node 32 b is located in therecovery fluid 308 stream so that therecovery fluid 308 receives the large particles 326 that are concentrated at the first node 324 b causing them to be carried by therecovery fluid 308 out of the “large particle” outlet (LPO) 330. Thesecond node 324 a is located in thebypass channel 304, and does not participate in the separation. - Referring now to the drawings and in particular to
FIG. 4A , another embodiment of the present invention is illustrated. The device uses multiple microfluidic channels running in parallel along the length of a microfluidic chip, separated by specifically-designed distances (the “wall thickness”). One of these multiple channels serves as the separation channel and has two inlets and two outlets. The ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the recovery fluid within the recovery fluid channel. The piezoelectric transducer may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry. In addition, multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip. - The embodiment illustrated in
FIG. 4A is designated generally by thereference numeral 400. Thedevice 400 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets. One of the two fluids is thesample fluid 412, and the other fluid is a “recovery”buffer 408, which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system. Channel depth (typically 100-300 μm), width (typ. 300-1000 μm), and wall thickness (typ. 10-40 μm) are determined for each chip based on the desired acoustic pressure fields, and fabricated by means of standard photolithography with anisotropic etching. The two fluids enter the separation channel through separate inlets, and the separated sample fractions are collected at the two outlets. - The present invention provides an ultrasonic microfluidic apparatus for separating
small particles 418 fromlarge particles 420 contained in thesample fluid 412. Asample input channel 410 is provided for conveying thesample fluid 412 containingsmall particles 418 andlarge particles 420 toward the separation area. A recoveryfluid input channel 406 containingrecovery fluid 408 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, therecovery fluid 408 contacts thesample fluid 412. Abypass fluid channel 204 containingbypass fluid 204 is located substantially parallel and adjacent the separation channel. Note that the bypass fluid channel is a wide channel compared to the bypass channel shown in the previously described embodiments. An acousticallytransparent wall 422 is located between thebypass channel 204 and theseparation channel 406. Thebypass channel 404 together with thewall 422 comprise an acoustic extension structure. - An
acoustic transducer 414 in contact with themicrofluidic chip 416 produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, theacoustic transducer 414 generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, thelargest particles 420 move toward thenode 424 b fastest. Positioning thenode 424 b within therecovery fluid 408 stream allows thelargest particles 420 to be carried out of thechip 416 with therecovery fluid 408, separating them from other sample components that remain in thesample 412 stream. - Referring now to
FIG. 4B , a cross section taken alonglines 4B ofFIG. 4A in the direction of the arrows is shown. The body of thechip 416 includes aglass cover plate 426. The body of thechip 416 and theglass cover plate 126 enclose thebypass fluid channel 404, thebypass fluid 402, therecovery fluid 408, and thesample fluid 412. The acousticallytransparent wall 422 maintains thebypass fluid 402 separate from therecovery fluid 408. - The
acoustic transducer 414 produces theacoustic nodes first node 424 a is located in therecovery fluid 408 stream so that therecovery fluid 408 receives thelarge particles 420 that are concentrated at the firstacoustic node 424 a causing them to be carried by therecovery fluid 408 out of the “large particle” outlet (LPO) 430. Thesecond node 424 b is located in the bypass channel and does not participate in the separation. - Referring now to the drawings and in particular to
FIG. 5A , another embodiment of the invention is illustrated wherein the stream of concentrated particles is positioned off-center in the fluid channel by means of a region of hydrogel adjacent the fluid channel. In this embodiment, rather than using a second fluid channel separated by a wall, a hydrogel is immobilized (by photopolymerization or by other means) within the searation channel. The ultrasound standing-wave pressure fields are optimized to transfer focused particles out of the sample stream and into the recovery fluid within the recovery fluid channel. The piezoelectric transducer may be driven at single or multiple frequencies to achieve the optimal node placement depending on the channel and wall geometry. In addition, multiple small piezoelectric transducers may be arranged to produce different sound fields in different regions of the chip. - The embodiment illustrated in
FIG. 5A is designated generally by thereference numeral 500. Thedevice 500 has an “H-filter” geometry in which two fluids are pumped side-by-side down a microfluidic separation channel with two inlets and two outlets. One of the two fluids, thesample fluid 512, contains the sample and the other fluid is a “recovery”buffer 508, which is an appropriate medium (water or buffer) into which focused particles are transferred, while the unfocused components remain in the sample and continue straight through the system. Channel depth (typically 100-300 micrometers), width (typ. 300-1000 micrometers), and wall thickness (typ. 10-40 micrometers) are determined for each chip based on the desired acoustic pressure fields, and fabricated by means of standard photolithography with anisotropic etching. The two fluids enter the separation channel through separate inlets, and the separated sample fractions are collected at the two outlets. - The present invention provides an ultrasonic microfluidic apparatus for separating
small particles 518 fromlarge particles 520 contained in thesample fluid 512. A sample input channel 510 is provided for conveying thesample fluid 512 containingsmall particles 518 andlarge particles 520 toward the separation area. A recoveryfluid input channel 506 containingrecovery fluid 508 is routed to convey the recovery fluid substantially parallel and adjacent the sample fluid. Within the separation channel, the recovery fluid contacts thesample fluid 512. Agel 502 is located substantially parallel and adjacent theseparation channel 506. Thegel 502 comprises an acoustic extension structure. - An
acoustic transducer 514 in contact with themicrofluidic chip 516 produces an ultrasound pressure field throughout these fluids. Properly tuned to match the geometric parameters of the channel, theacoustic transducer 514 generates a resonant standing wave within the fluid, creating one or more zones of minimal pressure amplitude (acoustic nodes) toward which particles are driven. The forces that particles experience are dependent on particle size; therefore, thelargest particles 420 move toward the node 424 fastest. Positioning thenode 524 within therecovery fluid 508 stream allows thelargest particles 520 to be carried out of thechip 516 with therecovery fluid 508, separating them from other sample components that remain in the sample stream. - Referring now to
FIG. 5B , a cross section taken alonglines 5B ofFIG. 5A in the direction of the arrows is shown. The body of thechip 516 includes aglass cover plate 126. The body of thechip 516 and theglass cover plate 126 enclose the gel 528, therecovery fluid 508, and thesample fluid 512. Theacoustic transducer 514 produces theacoustic node 524 in therecovery fluid stream 506 so that therecovery fluid 508 receives thelarge particles 520 that are concentrated at theacoustic node 524 causing them to be carried by therecovery fluid 508 out of the “large particle” outlet (LPO) 530. - While the invention may be susceptible to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and have been described in detail herein. However, it should be understood that the invention is not intended to be limited to the particular forms disclosed. Rather, the invention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the following appended claims.
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US14/659,825 US9321050B2 (en) | 2011-08-16 | 2015-03-17 | Microfluidic ultrasonic particle separators with engineered node locations and geometries |
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US20140216992A1 (en) | 2014-08-07 |
US20150196911A1 (en) | 2015-07-16 |
US8991614B2 (en) | 2015-03-31 |
US8727129B2 (en) | 2014-05-20 |
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